Histogram-based thoracic impedance monitoring

ABSTRACT

Systems and methods for monitoring pulmonary edema or other thoracic fluid status in a subject use thoracic impedance histogram information. An internal or external processor circuit receives the thoracic impedance histogram information and uses it to compute and provide a lung fluid status indication. The thoracic impedance histogram information can include a count, mean or median of a histogram bin or subrange of bins within the histogram range.

CLAIM OF PRIORITY

This application is a continuation of U.S. application Ser. No.11/853,590, filed Sep. 11, 2007, which is hereby incorporated byreference in its entirety.

TECHNICAL FIELD

This patent document pertains generally to medical systems and methods.More particularly, but not by way of limitation, this patent documentpertains to fluid monitoring systems and methods configured for usinghistogram-based information about one or more thoracicimpedance-indicative signal values to compute and provide a lung fluidstatus indication.

BACKGROUND

Excess thoracic fluid retention can take various forms and can havedifferent causes. As an example, eating salty foods can result inretaining excess fluid in the thorax and elsewhere. Another source ofthoracic fluid accumulation is pulmonary edema, which involves abuild-up of extravascular fluid in or around a subject's lungs.

One cause of pulmonary edema is congestive heart failure (“CHF”),sometimes referred to simply as “heart failure.” Heart failure is amajor health problem—it is estimated that 5 million people suffer heartfailure in the United States alone and it is believed to be growing atan approximate rate of 550,000 new cases each year due to, among otherthings, overall demographic aging. CHF can be conceptualized as anenlarged weakened heart muscle. The impaired heart muscle results inpoor cardiac output of blood. Consequently, pulmonary vascular pressuresmay be elevated to the point that fluid leaks from the pulmonarycapillaries into the lungs, affecting normal oxygen exchange. For thisreason, pulmonary edema can be an indicator of CHF.

Pulmonary edema can present a medical emergency that requires immediatecare. The outlook for pulmonary edema patients can be good if detectedearly and treated promptly. If left undetected, and consequentlyuntreated, pulmonary edema can lead to extensive hospitalization andeven death.

OVERVIEW

The present inventors have recognized, among other things, that oneproblem presented by worsening heart failure is its timely detection andtreatment. The present inventors have further recognized an unmet needfor enhanced sensitivity or specificity of ongoing chronic monitoringfor actual or impending excess fluid accumulation in the thoracic regionof a subject, such as the subject's lungs, before the need forhospitalization arises.

The present systems and methods can monitor lung fluid status, such asthe presence or absence of pulmonary edema, in a subject. This caninvolve using information about at least one thoracicimpedance-indicating signal characteristic. The impedance characteristicinformation can be stored histogram bins. Each histogram bin canrepresent a numerical subrange of an array of expected thoracicimpedance-indicating signal characteristic values. Each histogram bincan be configured to quantifiably store the occurrence of numericallyinclusive thoracic impedance-indicating characteristic signals measuredby an electrical impedance measurement circuit. In various examples, aninternal or external processor circuit includes an input to receiveinformation about one or more histogram bins or the characteristicsignal(s) stored therein. The processor circuit can be configured to usesuch information to compute and provide a lung fluid status indication.In some examples, the information about the histogram bin(s) used tocompute the lung fluid status indication includes a count, mean, ormedian of the thoracic impedance-indicating signal characteristicvalue(s) stored therein.

In Example 1, a system comprises an implantable medical deviceincluding, an electrical impedance measurement circuit configured tomeasure at least one thoracic impedance-indicating signal characteristicusing information about electrical energy injected between two or moreelectrodes and a potential difference created thereby between the sameor different two or more electrodes; and a memory circuit including anumber of histogram bins, each bin representing a subrange of thoracicimpedance-indicating signal characteristic values, the memory circuitconfigured for storing the at least one thoracic impedance-indicatingsignal characteristic into a histogram bin having a numericallyinclusive subrange; and a processor circuit including an input toreceive and use information about the at least one thoracicimpedance-indicating signal characteristic stored in the histogram toprovide a lung fluid status indication.

In Example 2, the system of Example 1 optionally comprises a triggercircuit to trigger a thoracic impedance-indicating measurementsynchronized with a refractory portion of a subject's cardiac cycle, thetrigger circuit comprising at least one of a timing circuit or a cardiacsensor circuit.

In Example 3, the system of at least one of Examples 1-2 optionallycomprises a posture sensor configured to produce a posture signalindicative of a posture of a subject, the posture sensor configured totrigger a thoracic impedance-indicating measurement when the posturesignal is indicative of a substantially upright orientation.

In Example 4, the system of at least one of Examples 1-3 is optionallyconfigured such that the memory circuit includes a counter circuitconfigured to increment a count of a histogram bin.

In Example 5, the system of Example 4 is optionally configured such thatthe processor circuit is configured to use information about the countof the histogram bin to compute and provide the lung fluid statusindication.

In Example 6, the system of at least one of Examples 1-5 optionallycomprises a histogram-selective circuit configured to select one or morehistogram bins representative of a reduced subrange of the histogram.

In Example 7, the system of Example 6 is optionally configured such thatthe processor circuit is configured to use information about the reducedsubrange to compute and provide the lung fluid status indication, thereduced subrange representing an upper-percentile of the histogram or anintra-percentile range of the histogram.

In Example 8, the system of Example 7 is optionally configured such thatthe information about the reduced subrange includes information about acentral tendency of information represented by the reduced subrange.

In Example 9, the system of at least one of Examples 1-8 optionallycomprises a comparator circuit configured to compute a deviation betweenone or more histogram bins previously received from the memory circuitand one or more corresponding baseline histogram bins havingsubstantially the same numerical subrange; the processor circuitoptionally configured to use information about the deviation to computeand provide the lung fluid status indication.

In Example 10, the system of Example 9 is optionally configured suchthat the deviation is indicative of a difference in the number of countsfrom the corresponding baseline histogram bin.

In Example 11, the system of Example 9 is optionally configured suchthat the deviation is between an average of thoracic impedance signalcharacteristic data of the one or more histogram bins previouslyreceived and thoracic impedance signal characteristic data of the one ormore baseline histogram bins.

In Example 12, the system of at least one of Examples 1-11 optionallycomprises an external user-interface device communicatively coupled tothe implantable medical device and including a user-detectableindication, the user-detectable indication configured to provide adisplay of at least one of received information about thoracic impedancesignal characteristic data of one or more histogram bins, a deviationtrend between such received information and corresponding information ofone or more baseline histogram bins, or the computed lung fluid statusindication.

In Example 13, a method comprises measuring a thoracicimpedance-indicating signal characteristic including a fluid statuscomponent; storing the thoracic impedance-indicating signalcharacteristic in a histogram that includes a plurality of histogrambins representing corresponding subranges of thoracicimpedance-indicating signal characteristic values; and computing andproviding a lung fluid status indication using histogram informationabout the thoracic impedance-indicating signal characteristic.

In Example 14, the method of Example 13 optionally comprises attenuatinga cardiac stroke component of the thoracic impedance-indicating signal.

In Example 15, the method of Example 14 is optionally configured suchthat attenuating the cardiac stroke component includes synchronizing thethoracic impedance-indicating signal measurement to a specified portionof a subject's cardiac cycle.

In Example 16, the method of at least one of Examples 13-15 optionallycomprises selecting one or more histogram bins representative of asubrange of the histogram; and using information about the one or morebins representative of the subrange to provide the lung fluid statusindication.

In Example 17, the method of at least one of Examples 13-16 optionallycomprises overwriting a first histogram comprising first histogram binswith a second histogram comprising second histogram bins, the secondhistogram comprising data acquired later in time than for the firsthistogram array.

In Example 18, the method of at least one of Examples 13-17 optionallycomprises alerting a subject to the presence of thoracic fluidaccumulation using the lung fluid status indication.

In Example 19, the method of at least one of Examples 13-18 optionallycomprises initiating or adjusting a regimen in response to the lungfluid status indication.

In Example 20, the method of at least one of Examples 13-19 optionallycomprises triggering the thoracic impedance-indicating signalcharacteristic measurement when a posture signal indicative of asubstantially upright orientation is measured.

In Example 21, the method of at least one of Examples 13-20 isoptionally configured such that storing the thoracicimpedance-indicating signal characteristic includes incrementing a countassociated with a histogram bin; and computing the lung fluid statusindication includes using count information from the histogram.

In Example 22, the method of Example 21 optionally comprises aggregatingcount information from each of the histogram bins; and using theaggregated count information to compute the lung fluid statusindication.

In Example 23, the method of at least one of Examples 13-22 isoptionally configured such that storing the thoracicimpedance-indicating signal characteristic includes storing the thoracicimpedance-indicating signal characteristic into a bin of an intradayhistogram.

In Example 24, the method of Example 23 optionally comprises aggregatingthoracic impedance-indicating signal characteristic information from aplurality of intraday histograms; and using the aggregated thoracicimpedance signal characteristic information to compute the lung fluidstatus indication.

In Example 25, the method of at least one of Examples 13-24 isoptionally configured such that computing the lung fluid statusindication includes computing a deviation between at least one histogrambin of a short-term histogram and at least one corresponding histogrambin of a baseline histogram.

In Example 26, the method of Example 25 optionally comprises updatingthe short-term histogram using a thoracic impedance-indicating signalcharacteristic measured over a first time period; and updating thebaseline histogram using a thoracic impedance-indicating signalcharacteristic measured over a second time period that is longer thanthe first time period.

In Example 27, the method of at least one of Examples 13-26 isoptionally configured such that computing the lung fluid statusindication includes recognizing whether a thoracic fluid accumulationevent is present.

In Example 28, the method of at least one of Examples 13-27 isoptionally configured such that computing the lung fluid statusindication includes recognizing whether pulmonary edema is present.

In Example 29, a system comprises means for measuring a thoracicimpedance-indicating signal characteristic including a fluid statuscomponent; means for storing the thoracic impedance-indicating signalcharacteristic in a histogram that includes a plurality of histogrambins representing corresponding subranges of thoracicimpedance-indicating signal characteristic values; and means forcomputing and providing a lung fluid status indication using histograminformation about the thoracic impedance-indicating signalcharacteristic.

The present systems and methods can enhance thoracic fluid monitoring byreducing data storage or signal processing needed. This can reduceimplanted device size or increase its longevity. The foregoing can bemade possible by, among other things, storing information about at leastone thoracic impedance-indicating signal characteristic in one of anumber of histogram bins. Each histogram bin can numerically represent adifferent subrange of thoracic impedance-indicating signalcharacteristic values from an expected range. Thoracic fluid monitoringcomplexity can be reduced by using information about a count of thoracicimpedance signal characteristic values stored in one or more of thehistogram bins to compute a lung fluid status indication. Thoracic fluidmonitoring can also be made more accurate, such as by using informationabout a selected portion of a histogram array. For example, informationabout an upper-quartile portion or intra-quartile portion of thehistogram array can be used to compute the lung fluid status indication.

These and other examples, advantages, and features of the present fluidmonitoring systems and methods will be set forth in part in followingDetailed Description. This Overview is intended to provide an overviewof subject matter of the present patent application. It is not intendedto provide an exclusive or exhaustive explanation of the invention. TheDetailed Description is included to provide further information aboutthe present patent application.

BRIEF DESCRIPTION OF THE DRAWINGS

In the drawings, like numerals may be used to describe similarcomponents throughout the several views. Like numerals having differentletter suffixes may be used to represent different instances of similarcomponents. The drawings illustrate generally, by way of example, butnot by way of limitation, various embodiments discussed in the presentdocument.

FIG. 1 is a block diagram illustrating examples of various causes andindications of pulmonary edema in a subject.

FIG. 2 is a schematic view of an example of a system configured formonitoring excess fluid accumulation in the thoracic region of a subjectby computing and providing a lung fluid status indication, theindication found using information organized and stored in one or morehistogram bins.

FIG. 3 is a schematic view illustrating an example implant site ofportions of a system configured for monitoring excess fluid accumulationin the thoracic region of a subject by computing and providing a lungfluid status indication, the indication found using informationorganized and stored in one or more histogram bins.

FIG. 4 is a block diagram illustrating an example of an implantablememory circuit used by a fluid monitoring system to organize and storeat least one thoracic impedance-indicating signal in one of a number ofhistogram bins.

FIGS. 5A-5B are block diagrams illustrating portions of an examplesystem configured for monitoring excess fluid accumulation in thethoracic region of a subject by computing and providing a lung fluidstatus indication, the indication found using information organized andstored in one or more histogram bins.

FIG. 6 is a graphical display illustrating an example of a histogramarray stored in a memory circuit, information of which can be used by afluid monitoring system to compute and provide a lung fluid statusindication.

FIG. 7 is a graphical display illustrating an example of a trend overtime of information stored in one or more portions of a histogram array,such trend indicative of present or impending fluid accumulation.

FIG. 8 is a block diagram illustrating an example of a regimen controlcircuit for use in the present system, the system being configured formonitoring excess fluid accumulation in the thoracic region of a subjectusing information organized and stored in one or more histogram bins.

FIG. 9 is a block diagram illustrating an example method of monitoringexcess fluid accumulation in the thoracic region of a subject bycomputing and providing a lung fluid status indication, the indicationfound using information organized and stored in one or more histogrambins.

DETAILED DESCRIPTION

Excess fluid accumulation in a region of a subject is typically referredto simply as “edema.” Edema can be conceptualized as a failure ordecompensation of one or more homeostatic processes within the subject'sbody. The body normally prevents the accumulation of fluids therewithinby maintaining adequate pressures and concentrations of salts andproteins, and by actively removing excess fluid. If a disease affectsany of these normal bodily mechanisms or if the normal bodily mechanismsare unable to keep up with the fluid accumulation, the result can beedema, such as pulmonary edema.

There are several conditions or diseases that can cause or affectpulmonary edema. As shown in FIG. 1, this includes, among others, heartfailure 102, left-sided myocardial infarction 104, high blood pressure106, altitude sickness 108, emphysema 110, cancers that affect thelymphatic system 112, diseases that disrupt protein concentrations 114,or epithelial pathologies 116, such as those caused by inhalation oftoxic chemicals, leading to flooding of the alveoli. While pulmonaryedema 100 can be a sign of many conditions or diseases, the prospectthat pulmonary edema 100 can be a sign of failing heart circulation 102is often of first concern to caregivers (e.g., health careprofessionals) due to the severity of its nature. Unfortunately, thefirst indication that an attending caregiver typically has of anoccurrence of pulmonary edema 100 is very late in the disease process,such as when it becomes physically manifested by swelling 118,noticeable weight gain 120, jugular venous distension 122, or breathingdifficulties 124 that are so overwhelming as to be noticed by thesubject, who then proceeds to be examined by his or her caregiver. For aheart failure subject, hospitalization at such a physically apparenttime will likely be required.

In an effort to timely and accurately detect impending edema, such aspulmonary edema, and avoid its associated hospitalizations, the presentambulatory fluid monitoring systems and methods compute and provide alung fluid status indication using information about at least onethoracic impedance-indicating signal characteristic stored in one of anumber of histogram bins. Each histogram bin represents a numericalsubrange of an array of expected thoracic impedance-indicating signalcharacteristic values, and is configured to quantifiably store theoccurrence of numerically inclusive thoracic impedance-indicating signalcharacteristics measured by an electrical impedance measurement circuit.For each thoracic impedance-indication signal characteristic valuestored in a given histogram bin, a count of values for that bin isincremented. Thus, over a given time period, many measurements can beefficiently stored. This histogram-based information, upon storing, canthereafter be used to estimate the probability distribution or summarystatistics of thoracic impedance-indicating values for the given timeperiod. This can be used to compute and provide a lung fluid statusindication having potentially enhanced sensitivity (e.g., effectivelydetect a condition that a user desired to detect or treat) orspecificity (e.g., avoid erroneous or “false” detections of thecondition that a user desires to detect or treat).

Examples

FIG. 2 shows a heart 202 and lungs 204 (left), 206 (right) of a subject208 (via a cut-away portion 210), and an example of an ambulatory system200 configured for monitoring excess fluid accumulation in a thoracicregion, such as the lungs. The monitoring can use information about atleast one thoracic impedance-indicating signal characteristicimplantably stored in one of a plurality of histogram bins. In variousexamples, such monitoring can occur in the comfort of one's own home280. Each histogram bin represents a numerical subrange of a range ofthoracic impedance-indicating signal characteristic values. Eachhistogram bin can be configured to quantifiably store the occurrence ofnumerically inclusive thoracic impedance-indicating signalcharacteristics, such as can be measured by an electrical impedancemeasurement circuit.

In FIG. 2, the system 200 includes a pectorally-implanted medical device(IMD) 212, which is coupled via one or more electrode-bearing leads 214to the heart 202 of the subject 208. In this example, the system 200 canalso include one or more programmers, medical data storage systems 270,or other external user-interface devices 216 (nearby), or 218 (distant)providing communications with the IMD 212, such as by using telemetry220 or another communication network 222. As shown, the one or moreexternal user-interface devices 216, 218 can include, among otherthings, a user-detectable indication 224, a user input device 226, and aprocessor circuit 230. The user-detectable indication 224, such as anLCD or LED or other display, can textually or graphically relayinformation collected by the IMD 212 or information about a lung fluidstatus indication computed by the processor circuit 230 using the IMDcollected information. The user input device 226 is configured forreceiving programming information from a user and communicating theprogramming information to the IMD 212. A wearable device 228 can beused to extend the communications range between the IMD 212 and thenearby external user-interface device 216 or the communication network222 without substantially increasing battery usage of the IMD 212.

As shown, the IMD 212 can include a housing 232 that houses theelectrical impedance measurement circuit 250 configured for measuringthe at least one thoracic impedance-indicating signal characteristic anda memory circuit 252 configured for implantably storing the at least onethoracic impedance-indicating signal characteristic in one of a numberof histogram bins having a numerically inclusive subrange. The IMD 212can include a left ventricular port in a header 234 thereof forreceiving a proximal end of an electrode-bearing left ventricular lead214. A distal end of the left ventricular lead 214 can be introducedinto the venous system, down the superior vena cava, into the rightatrium 236, into a coronary sinus through an orifice 238, and thenfurther into a coronary vein, which runs epicardially over the leftventricle 240.

In the example shown, the left ventricular lead 214 includes twoelectrodes 242, 244 that are electrically connected to respectiveconductors that run through the lead 214. The conductors connect toconducting wires within the IMD 212 when the left ventricular lead 214is received by the left ventricular lead port, thereby establishingelectrical connections between the electrical impedance measurementcircuit 250 and the electrodes 242, 244. In this example, the electrode242 can be referred to as a left ventricular proximal electrode, whileelectrode 244 can be referred to as a left ventricular distal electrode,due to their relative positioning on the left ventricular lead 214.While the left ventricular lead 214 shown in FIG. 2 is bipolar innature, the lead 214 can optionally include additional or fewerelectrodes and can further follow a different path through the heart 202from that shown and described.

A housing electrode 254 on an exterior surface of the IMD housing 232can be electrically connected to the electrical impedance measurementcircuit 250 to complete a tripolar electrode configuration in whichelectrical energy (e.g., current) is injected between a lead electrode,such as the left ventricular distal electrode 244, and the housingelectrode 254, and a potential difference (i.e., voltage) created by theinjected energy can be measured between the other lead electrode—in thisexample, the left ventricular proximal electrode 242—and the housingelectrode 254. The IMD 212 can optionally include a second housing orheader electrode 256 to facilitate a tetrapolar electrode configurationin which electrical energy is injected, for example, between a the leftventricular distal electrode 244 and the housing electrode 254, and aresponsive potential difference created by the energy is measuredbetween the left ventricular proximal electrode 242 and the headerelectrode 256. Using information about the injected electrical energyand the resulting potential difference, an impedance calculator (e.g.,within the electrical impedance measurement circuit 250) can calculate athoracic impedance-indicating signal characteristic such as by takingthe ratio of measured voltage to injected current. Animpedance-indicating signal characteristic, such as amplitude of theimpedance signal, for example, can then be communicated to memory 252for storing in the appropriate one of a number of histogram bins, suchas by incrementing the count of the histogram bin representing animpedance range into which the measured impedance amplitude falls.

FIG. 3 illustrates that the IMD 212 can include not only a leftventricular port in the header 234 thereof for receiving the proximalend of the left ventricular lead 214, but can also include a rightatrial port for receiving a proximal end of an electrode-bearing rightatrial lead 302. A distal end of the right atrial lead 302 is shown inthis example as being introduced into the venous system, down thesuperior vena cava, and into the right atrium 236. In the example shown,the right atrial lead 302 includes two electrodes 304, 306 that areelectrically connected to conductors that run through the lead 302. Theconductors connect to conducting wire within the IMD 212 when the rightatrial lead 302 is received by the right atrial lead portion, therebyestablishing electrical connections between the electrical impedancemeasurement circuit and the electrodes 304, 306. In this example, theelectrode 304 can be referred to as a right atrial proximal electrode,while electrode 306 can be referred to as a right atrial distalelectrode, due to their relative positioning on the right atrial lead302. While the right atrial lead 302 shown in FIG. 3 is bipolar innature, the lead 302 can optionally include additional or fewerelectrodes and can follow a different path through the heart 202 fromthat shown.

Including the right atrial lead 302 in FIG. 3 provides a tetrapolarelectrode configuration for measuring thoracic impedance-indicatingsignal characteristics. In such an example, electrical energy can beinjected between the housing electrode 254 and the left ventriculardistal electrode 244. A potential difference created by the energy canbe measured between left ventricular proximal electrode 242 and one ofthe right atrial proximal electrode 304 or the right atrial distalelectrode 306. In this example, should the left ventricular lead 214 notbe available, thoracic impedance-indicating signal characteristics canstill be measured, such as by injecting electrical energy between thehousing electrode 254 and the right atrial distal electrode 306. Apotential difference created by the energy can be measured between thehousing 254 or header 256 electrode and the right atrial proximalelectrode 304.

The human body includes a number of thoracic organs, tissues, andfluids. Measurement of thoracic impedance can include contributions fromeach. For example, resistivities of the heart muscle, lungs, pectoralmuscle, pectoral fat, liver, kidneys, spleen, stomach, skeletal muscle,bone, cartilage, blood and other tissues and fluids each can contributeto a measurement of thoracic impedance. As such, changes in measuredthoracic impedance can be caused by changes in the resistivities ofthese and other organs or tissues.

Thus, when measuring impedance, such as thoracic impedance, to detect orassess one or more pathologies or conditions, such as pulmonary edema,it can be desirable to measure the impedance-indicating signals usingone or more electrode configurations that are more sensitive to aparticular region(s) of interest. In the examples of FIGS. 2-3,placement of the left ventricular lead 214 and the right atrial lead 302near the left ventricle 240 and the right atrium 236 of the heart 202,respectively, provide an example of a suitable location for measuringthoracic impedance, and more specifically heart and lung impedance, dueto the proximity of the heart and lungs 204, 206 thereto. Although notshown, a right ventricular lead having right ventricular electrodes canalso be used in one or more thoracic impedance measurementconfigurations.

In various examples, the electrical impedance measurement circuit 250within the IMD 212, in conjunction with the lead 214, 302, header 256,or housing 254 electrodes, measure thoracic impedance-indicating signalcharacteristics by injecting a relatively small amplitude electricalenergy (e.g., a current) between at least two implanted electrodes andconcurrently measuring an responsive induced potential difference (i.e.,a voltage) between the same or different at least two implantedelectrodes, such as discussed above. Because the magnitude of theinjected electrical energy is typically specified, the measurement ofthe responsive potential difference allows for a thoracicimpedance-indicating signal characteristic measurement to be determined,such as from Ohm's law (e.g., by taking a ratio of measured voltage toinjected current).

In various examples, the thoracic impedance-indicating signalcharacteristic measured includes—listed in order from generally higherfrequencies to generally lower frequencies—information about thesubject's heart contractions (stroke component), the subject's breathing(respiration component), and the subject's edema (fluid statuscomponent). As fluid accumulates in the lungs due to pulmonary edema,such as from a low fluid level to a higher fluid level, theimpedance-indicating signal decreases in value permitting pulmonaryedema to be detected. Without being bound by theory, it is believed thatthe respiration component may also be affected by thoracic fluidaccumulation.

The IMD 212 can include one or both of a timing or cardiac sensorcircuit (see FIG. 5A) to synchronize impedance sampling to occur at aparticular portion of the subject's cardiac cycle, such as within arefractory portion of the subject's cardiac cycle. During suchrefractory periods, sense amplifiers for detecting the intrinsicelectrical heart signals are “blanked” or otherwise configured to beless likely to detect intrinsic electrical depolarizations that areindicative of intrinsic heart contractions. This avoids the possibilityof the delivered test current somehow being erroneously detected by suchsense amplifiers as indicating an intrinsic electrical depolarizationcorresponding to an intrinsic heart contraction. Such an erroneousdetection, in turn, could trigger delivery of inappropriate responsivetherapy. Synchronizing thoracic impedance sampling to a refractoryportion of a cardiac cycle is consistent with established techniques forthoracic impedance sampling, such as thoracic impedance determination ofa minute ventilation signal for controlling pacing rate of arate-responsive pacer. Because no analogous difficulties exist withrespect to the respiration component of the thoracic impedance signal,the measured thoracic impedance signal need not be synchronized to aparticular portion of the respiration cycle of the measured thoracicimpedance signal. Therefore, the measured impedance signal generally caninclude at least a respiration component.

FIG. 4 is a block diagram illustrating one conceptual example of animplantable memory circuit 252 that can be used by the present fluidmonitoring system 200. A classification circuit 402 of the memorycircuit 252 is configured to organize and store digitized thoracicimpedance-indicating signal characteristic measurements in one of anumber of bins collectively comprising a histogram. The histogram can bedivided into a programmable number of bins (e.g., 255 bins). Each bincan represent a corresponding subrange of thoracic impedance-indicatingsignal characteristic amplitude values. Each bin can also include acorresponding count representing the number of samples detected during aparticular time period that fell within the subrange of that bin. Incertain examples, this count can be implemented as a memory locationstoring a count value. In certain examples, such bin count memorylocations can be included in a counter circuit 404 that increments theappropriate bin's count of the number of impedance samples falling intothat bin's subrange of values. Using the histogram approach, over agiven time period many measurements can be efficiently stored in thehistogram. The histogram, or portions thereof, can be used to estimatethe probability distribution or summary statistics of the impedancevalues for the given time period.

In an example, the bins collectively form an intraday histogram. Theintraday histogram can store part of a day's worth of thoracicimpedance-indicating signal characteristic data. A new intradayhistogram array can be acquired and populated with impedance signalmeasurements several times daily, if desired. In some examples, the IMD212 (FIG. 2) can store about 90 days worth of intraday histograms in abuffer, and after 90 days, can overwrite the oldest histograms withnewly acquired histograms. A daily or other short-term histogram canalso be computed in certain examples, such as directly or by aggregatingthat day's intraday histograms, for example. In various examples, aninternal or external processor circuit includes an input to receivethoracic impedance histogram information, and is configured to use suchinformation to compute and provide a lung fluid status indication, suchas further discussed below.

FIGS. 5A-5B are block diagrams illustrating generally, by way ofexample, but not by way of limitation, portions of an example system 200configured for using thoracic impedance histogram information formonitoring fluid accumulation status in a subject's thoracic region,such as a subject's left 204 or right 206 lungs. In this example, thesystem 200 includes a hermetically sealed IMD 212 coupled to a subject'sheart 202 such as by one or more electrode-bearing intravascular leads.The example of FIG. 5A illustrates use of a left ventricular lead 214having electrodes 242, 244 or a right atrial lead 302 having electrodes304, 306. As shown in FIG. 5B, the system 200 can further include one ormore programmers or other external user-interface devices 216 (nearby),218 (distant). The IMD 212 includes circuitry for, among other things,measuring thoracic impedance-indicating signal characteristics,efficiently storing the impedance-indicating signals, and interfacingwith external components.

In the example of FIG. 5A, an electrical impedance measurement circuit250 can include an injected electrical energy generator circuit 508, avoltage measurement circuit 510, an analog-to-digital (A/D) converter,and a calculation circuit 512 to compute and provide a thoracicimpedance-indicating signal characteristic to a memory circuit 252 forefficient storage, as discussed above for FIG. 4. The electrical energygenerator circuit 508 can be configured to generate and inject asub-stimulation current or other electrical energy between at least twoelectrodes, such as excitation electrodes (e.g., left ventricular distalelectrode 244 and can electrode 254). In one example, the injectedcurrent is AC in nature and has a frequency of about 4 KHz-100 KHz.

The injection current creates an electric field in a subject's body.Thus, a voltage potential appears between, for example, the leftventricular proximal electrode 242 and header electrode 256. A voltagemeasurement circuit 510 is configured to then measure this voltagebetween electrodes 242 and 256, for example. The voltage measurementcircuit 510 can include a demodulator. In various examples, theparticular electrodes used to inject the energy and to measure theresulting potential difference can be selected by an electrodeconfiguration switch circuit 516.

The calculation circuit 512 receives, measures, or includes informationon the magnitudes of both the injected current and the resultingmeasured voltage. An analog-to-digital (A/D) converter, within oroutside of the calculation circuit 512, can be used to translate theinformation. Other signal processing or frequency-selective filteringcan (but need not) be performed. Once digitized, these values can beapplied as inputs to the calculation circuit 512 for calculating athoracic impedance-indicating signal characteristic, such as by dividingthe measured voltage by the injected current. As body tissue fluidlevels increase, the tissue impedance decreases. Thus, the impedance canbe used to assess pulmonary edema, and a degree of pulmonary edema canbe determined for the subject.

Information from one or more sensor circuits, such as a posture sensorcircuit 520, a cardiac sensor circuit 522, or a respiration sensorcircuit 524, can be input to an internal processor circuit 514 and usedto adjust the relationship (via a state correction circuit 526) betweenthe measured thoracic impedance-indicating signal characteristics andthe degree of edema or ensure certain impedance sampling parameters aremet. For instance, the posture sensor circuit 520 may provide subjectorientation information to the state correction circuit 526. This allowsposture compensation to be included in the assessment of edema. Becauseorgans and excess fluid in the thorax and lungs can shift with posturechanges due to gravity, measured impedance may vary as a subject 208(FIG. 2) assumes different positions. For example, when a subject 208lies on his/her right side, fluid and tissues in the left lung 204 maygravitate towards the mediastinum near the left ventricular leadelectrodes 242, 244 resulting in lower measured impedance. Thus, basedon posture sensor information, the relationship between theimpedance-indicating signal measurement and the degree of edema may beadjusted to compensate. Similarly, that relationship may be inverselyadjusted for a subject lying on his/her left side. One or more ofseveral types of posture sensors could be used, including one or anycombination of a mercury switch, a tilt switch, a single axisaccelerometer, a multi-axis accelerometer, or piezoresistive or otherdevices.

A respiration sensor circuit 524, such as a minute ventilation (MV)sensor, motion sensor, strain gauge on the diaphragm, or other activitysensor, can also provide information to the state correction circuit526. The respiration sensor circuit 524 can provide breathing cycleinformation to the state correction circuit 526. This information can beused for verifying that an impedance sampling period is greater acorresponding respiration cycle, such as to ensure that one or morerespiratory components are retained and included in thethoracic-impedance indicating signal, if desired.

The IMD 212 can further include a timing 550 or other circuit, such asthe cardiac sensor circuit 522 that can detect cardiac rate oramplitude, such as to synchronize impedance sampling to a specifiedportion (e.g., a refractory portion) of the subject's cardiac cycle.This helps reduce the chance of the delivered impedance test currentbeing erroneously detected as a heart depolarization by sense amplifiersfor detecting intrinsic electrical heart signals. Any of the sensors520, 522, or 524 can optionally be excluded from the IMD 212.

A communication circuit 506 within the IMD 212 can be configured forwirelessly communicating with a communication circuit of the nearbyexternal user-interface device 216. In certain examples, thecommunication circuit 506 is configured for wirelessly communicatingwith a communication circuit of a distant external user-interface device218, such as by using a nearby external communication repeater 570. Inone such example, the external communication repeater 570 is coupled tothe distant external user-interface device 218 such as via an Internetor telephone communication network 222. The Internet or telephonecommunication network 222, in certain examples, allows the externalcommunication repeater 570 to communicate with electronic medical datastorage system 270.

The external user-interface devices 216, 218 can include, among otherthings, an input 572 to receive thoracic impedance histogram informationfrom the memory circuit 252 and an external processor circuit 230 to usesuch received information to compute and provide a lung fluid statusindication. The external user-interface devices 216, 218 can furtherinclude a user-detectable indication 224, such as for textually orgraphically relaying information collected via input 572 or informationabout the lung fluid status indication computed by the processor circuit230. In addition, the external user-interface devices 216, 218 caninclude a user input device 226 for receiving programming informationfrom a user and communicating the programming information to the IMD212.

To compute and provide the lung fluid status indication, the externalprocessor circuit 230 can include a histogram-selective circuit 580, acalculation circuit 582, a comparator circuit 584, and a fluidaccumulation determination circuit 554. The histogram-selective circuit580 can be configured to select one or more histogram binsrepresentative of certain histogram portion, such as an upper-quartilehistogram portion, for use in computing the lung fluid statusindication. The calculation circuit 582 can be configured to receive theselected one or more histogram bins to extract a signal count or computea mean or median or other measure of central tendency of thoracicimpedance-indication signal characteristic counts stored in such binssuch as by using statistical analysis.

The count, mean, median or the like can then be output to the comparatorcircuit 584, such as for comparison with a stored specified baselinethreshold, algorithm, pattern, or histogram, each of which can be basedon a subject in a non-edemic state. An initial stored baseline can bepreprogrammed into the comparator 584, and thereafter adjusted up anddown using recently measured and stored thoracic impedance-indicatingsignal characteristic data. It can be determined whether the output dataexhibits a characteristic of present or impending lung fluidaccumulation, such as an indication that a deviation between the outputdata and the baseline is beyond some programmed limit, for example. Ifthe deviation extends beyond such limit, the resulting comparison can beforwarded to a fluid accumulation determination circuit 554. The fluidaccumulation determination circuit 554 can be configured to use suchinformation to provide a lung fluid status indication, such as anindication of present or impending lung fluid accumulation.

In one example, the comparator circuit 584 is configured to compute adeviation between one or more portions of a daily histogram array and abaseline histogram array using the following equation:

$\begin{matrix}{{{\Delta \; z_{n}} = {\frac{1}{C_{n}}{\sum\limits_{i = 1}^{I}{z_{i}\left( {c_{ni} - {\frac{C_{n}}{B_{n}}b_{ni}}} \right)}}}},} & \left\lbrack {{Equation}\mspace{14mu} 1} \right\rbrack\end{matrix}$

where c_(ni) represents the count in the ith histogram bin of the nthday's daily histogram array, b_(ni) represents the count in the ith binof the baseline histogram array, C_(n) is the total number of thecurrent day's daily histogram array counts, B_(n) is the total number ofthe baseline histogram array counts, I is the total number of histogramarray bins, and z_(i) is the thoracic impedance-indication signal valuecorresponding to the ith bin. If the above equation yields a value belowa specified threshold value, then the fluid accumulation determinationcircuit 554 declares an indication of fluid accumulation to exist. Thisindication of fluid accumulation can be the sole basis of issuing analert to a user, or it can be combined or otherwise used with one ormore other indications, referred to as “detection enhancements.”

A first such “detection enhancement” integrates a negative differencebetween Δz_(n) and the specified threshold value, such as over a periodof multiple days. If this integrated value exceeds a specified(different) threshold value, then an indication of fluid accumulation isdeclared.

In a second detection enhancement technique, one or more rules require mout of n of the most recent Δz_(n) samples to meet the specifiedthreshold value before declaring the occurrence of a thoracic fluidaccumulation event. In such a case, a single threshold crossing can bereferred to as a “tentative event.” No alert is provided until m out ofthe last n days meet the threshold, which is then deemed an actual fluidaccumulation event. Multiple such m of n rules may be concurrentlyemployed, e.g. three out of three, three out of four, three out of five,three out of six, four out of seven, etc.

The specified threshold value, to which Δz_(n) is compared, can beobtained using a Constant False Alarm Rate (CFAR) detection technique.At least one example of a suitable CFAR detection technique is describedin commonly-owned Siejko et al., U.S. patent application Ser. No.11/276,735, entitled “PHYSIOLOGICAL EVENT DETECTION SYSTEMS ANDMETHODS,” which is incorporated herein by reference in its entirety. Thecaregiver specifies a maximum acceptable rate of false alarms (e.g., 1%)that the caregiver is willing to tolerate. If the baseline histogram hasbeen acquired during a time period that is free of any fluidaccumulation events, this baseline histogram can be used as aprobability density function (PDF). The user-specified maximumacceptable rate of false alarms maps to a tail area under the PDF curveprovided by the event-free baseline histogram. A boundary of the tailarea corresponds to the specified threshold value, against which Δz_(n)is compared. Thoracic impedance-indicating signal characteristic valuesdetected in the bins corresponding to the defined tail of thedistribution represent evidence of fluid accumulation events. Since thebaseline histogram can change over time, the specified threshold valuecan be periodically or recurrently re-computed. Such re-computationeffectively provides an adaptive threshold that remains consistent withthe user-specified maximum acceptable false alarm rate.

In addition to the fluid accumulation alert described above, theexternal processor circuit 230 can be capable of computing arepresentative fluid index value from the daily histogram data arrayreceived from the IMD 212. A trend of the representative fluid indexvalue (e.g., over several or many days) can be displayed for thesubject, caregiver, or other user. Advantageously, by externallyprocessing the histogram-stored thoracic impedance information, theIMD's 212 battery life may be prolonged. Notably, internal processing ofthe histogram-stored thoracic impedance information can also be foundadvantageous in certain situations, such as in situations whereclosed-loop systems for disease detection and responsive therapy arewarranted and desired.

In various examples, the system 200 can include a regimen controlcircuit 552 configured for initiating or adjusting a regimen to asubject 208 (FIG. 2) at least in part by using thoracic impedancehistogram information or an indication of present or impending lungfluid accumulation (e.g., a lung fluid status indication) externallycomputed from such information and output by a fluid accumulationdetermination circuit 554. In an example, such regimen includeselectrical stimulation, such as cardiac pacing, resynchronization,cardioversion, or defibrillation stimulation, generated by a regimenpulse generator circuit 502 and delivered via one or more electrodesselected by the electrode configuration switch circuit 516. The one ormore electrodes can be selected individually or in combination to serveas an anode or a cathode in any unipolar, bipolar or multipolarconfiguration.

In another example, such regimen is provided elsewhere (e.g.,communicated to the nearby external user-interface 216 or delivered viaan implantable drug pump 504) and includes, for example, a drug dose, adiet regimen, or a fluid intake regimen. In one example, the drug dosecan include a set of one or more drug regimen instructions communicatedand displayed on the nearby external user-interface 216, such as in theform of the user-detectable indication 224. In certain examples, the setof drug regimen instructions includes a suggested daily intake scheduleof one or more drugs, such as antiotension-converting enzyme (ACE)inhibitors, beta blockers, digitalis, diuretics, vasodilators, or thelike. In certain examples, the drug dose can be automatically deliveredper the suggested daily intake schedule via the implantable drug pump504 or another drug dispensing device provided within the IMD 212 orimplanted nearby and coupled thereto. In certain examples, the drug dosecan be delivered per the suggested daily intake schedule via external(e.g., electronic) drug dispersing devices.

In a similar manner, the diet regimen and the fluid intake regimen canbe communicated to the subject 208 via the user-detectable indication224 of the nearby external user-interface 216. In an example, the dietregimen can include a set of one or more dietary instructions to befollowed by the subject 208, such as restriction of sodium to 2 grams orless per day and no more than one alcoholic drink per day. In anotherexample, the fluid intake regimen can include a set of one or more fluidintake instructions to be followed by the subject 208, such as to avoidconsuming an excess amount of fluid. FIGS. 5A-5B illustrate just oneexample of various circuits, devices, and interfaces of the system 200,which are implemented either in hardware or as one or more sequences ofsteps carried out on a microprocessor or other controller. Suchcircuits, devices, and interfaces are illustrated separately forconceptual clarity; however, it is to be understood that the variouscircuits, devices, and interfaces of FIGS. 5A-5B need not be separatelyembodied, but can be combined or otherwise implemented. As an example,an internal or an external processor circuit can include an input toreceive thoracic impedance histogram information, and can be configuredto use such information to internally or externally compute and providea lung fluid status indication.

FIG. 6 is a graphical display illustrating a histogram 600, such as anintraday histogram, stored in a memory circuit 252 (FIG. 2). Thehorizontal axis of the histogram 600 lists the impedance bin subranges.The vertical axis indicates the relative number of signal counts presentin each subrange. In this example, the histogram 600 includes eighthistogram bins (bin #1, bin #2, . . . , bin #8). Each such binrepresents a subrange of expected thoracic impedance-indicating signalcharacteristic amplitude values. Each such bin is configured toquantifiably store the occurrence of numerically inclusive thoracicimpedance-indication signals measured by an electrical impedancemeasurement circuit 250 (FIG. 2). For each thoracic impedance-indicationsignal value acquired that corresponds to the subrange of a givenhistogram bin, a count of values for that bin can be incremented. Asshown in FIG. 6, bin #1 has a count of approximately C₁, bin #2 has acount of approximately C₃, bin #3 has a count of approximately C₅, bin#4 has a count of approximately C₇, bin #5 has a count of approximatelyC₇, bin #6 has a count of approximately C₄, bin #7 has a count ofapproximately C₂, and bin #8 has a count of approximately C₁. Asdiscussed above, an external processor circuit 230 (FIG. 2) isconfigured to receive and use such thoracic impedance histograminformation to compute and provide a lung fluid status indication.

FIG. 7 is a graphical display illustrating a conceptualized (not realdata) trend 700 over time of impedance summary information computed fromone or more portions of a histogram array, such as an upper-quartileportion of the histogram array (see, e.g., bins #7 and #8 of FIG. 6). Inthe example shown, the impedance summary information from the one ormore portions of the histogram array has a decreasing trend over time. Adecreasing trend in histogram-based impedance values can indicatepresent or impending fluid accumulation, such as pulmonary edema. Theupper-quartile portion of the histogram array is representative ofhigher thoracic impedance-indicating signal characteristic values thanthe remaining quartiles of the histogram array. Thus, a reduction overtime in the number of counts, mean, median or the like of the upperquartile portion of the impedance histogram can indicate a shift of thehistogram toward lower impedance signal values. This can correlate to anindication of present or impending fluid accumulation in the lungs 204,206 (FIG. 2). Information about such a decrease can be used by thepresent system 200 (FIG. 2) to further specify an indication of lungfluid status. The graphical display illustrating the trend 700 over timecan be received and displayed on an external user-interface device 216,218 (FIG. 2), such as on an user-detectable indication screen 224.

Without being bound by theory, the present inventors have recognizedthat an upper-quartile portion of a histogram may exhibit the largestdiurnal variation when comparing thoracic fluid status levels between ahealthy (baseline) subject to a fluid overload subject. This is becausehigher thoracic impedance signal values are typically measured two,three or more hours after a subject wakes from a supine sleep position.After awaking, the subject will often assume some sort of uprightposture position in which fluid that has flowed toward the thoracicregion during supine sleep slowly drains away from such region overtime. For healthy subjects, the increase in thoracic impedance duringsuch time is relatively large; however, for fluid overload subjects, theincrease in thoracic impedance may less pronounced. Thus, it is believedthat comparing a fluid overload subject's largest measured short-termthoracic impedance-indicating signal characteristic values (e.g., meanor median of the histogram's upper-quartile) or number of upper-quartilebin counts to that of a healthy baseline subject may provide a user withenhanced fluid accumulation status information, such as for determiningthe presence or absence of pulmonary edema. One or more of a sleep statedetector circuit, an activity sensor circuit, or a posture sensorcircuit 520 (FIG. 5A) can be used to recognize sleep and awake subjectstates.

There are a variety of underlying conditions that may lead to thoracicfluid build-up, more specifically pulmonary edema, and a variety ofregimen approaches targeting such conditions. The selection of theregimen approach, and the parameters of the particular regimen approachselected, can be a function of the underlying condition and a severityof such condition. For this reason, the present system 200 (FIG. 2) caninclude a regimen control circuit 550 to appropriately select a regimengiven a subject's detected health status.

FIG. 8 is a block diagram illustrating an example of a regimen controlcircuit 552, which can be used to trigger one or more regimens (e.g.,therapies) to a subject 208 (FIG. 2). A regimen can be triggered inresponse to thoracic impedance histogram information or a resultingindication of present or impending lung fluid accumulation statusindication. The fluid status indication can be externally computed fromsuch information and output by a fluid accumulation determinationcircuit 554.

The regimen control circuit 552 can include an input that receives theindication of present or impending lung fluid accumulation output fromthe fluid accumulation determination circuit 552. In an example, ascheduler 802 schedules the indications of present or impending lungfluid accumulation. A regimen decision circuit 804 decides whether someform of regimen is warranted. If a regimen is deemed to be warranted, aregimen selection circuit 806 selects one or more appropriate regimens.A control circuit 808 adjusts the selected regimen via an output to oneor more of a regimen pulse generator circuit 502, a nearby externaluser-interface 216, or a drug pump 504, for example.

The regimen control circuit 552 can include a regimen list 810, whichcan relate the regimens of such list 810 to the highest contributor(s)to the indication of present or impending lung fluid accumulation. In anexample, the regimen list 810 includes all possible disease statepreventive regimens or secondarily related regimens that the presentsystem 200 can deliver or communicate to the subject 208. The regimenlist 810 can be programmed into an IMD 212 (FIG. 2) either in hardware,firmware, or software and stored in a memory 252 (FIG. 2).

In another example, the regimen list 810 includes immediate, short-term,intermediate-term, or long-term fluid accumulation preventive therapies.Immediate fluid accumulation preventive therapies can include, by way ofexample, initiating or changing a drug dose administered to the subjectvia an implantable drug pump 504 or electrical stimulation administeredto the subject 208 via the regimen pulse generator circuit 502.Short-term fluid accumulation preventive regimens can include, by way ofexample, administering a continuous positive air pressure (“CPAP”) doseto the subject 208 or notifying a caregiver to initiate or change thesubject's drug dose treatment program. Intermediate-term fluidaccumulation preventive regimens can include, by way of example,adjusting the subject's 208 lifestyle such as his or her diet or fluidintake regimen. Finally, long-term fluid accumulation preventiveregimens can include, by way of example, notifying the subject 208 orcaregiver to alter the drug which takes longer to affect the subject(e.g., beta blockers, ACE inhibitors) or administering CRT to thesubject 208.

Each member of the regimen list 810 can be associated with acorresponding time of action, which can include information about one ormore of a time for the regimen to become effective or a time after whichthe regimen is no longer effective. In one example, only one member ofthe regimen list 810 is invoked at any particular time. In anotherexample, one or more combinations of different regimens are provided atsubstantially the same time. The various subcircuits in the regimencontrol circuit 552 are illustrated as such for illustrative purposesonly; however, these subcircuits can alternatively be incorporated inthe fluid accumulation determination circuit 554 or elsewhere, such asbeing implemented as a set of programmed instructions performed by ageneral purpose controller or other circuit.

FIG. 9 is a block diagram 900 illustrating one example of a method ofmonitoring excess fluid accumulation in the thoracic region of asubject. This can involve monitoring one or both of a subject's lungsusing thoracic impedance histogram information. Each histogram binrepresents a subrange of expected thoracic impedance-indicating signalcharacteristic values. Each histogram bin can be configured toquantifiably store the occurrence of numerically inclusive thoracicimpedance-indicating signal characteristic measurements measured by anelectrical impedance measurement circuit. At 902, one or more thoracicimpedance-indicating signal characteristics including at least arespiration component and a fluid status component are measured. At 904,a cardiac stroke component of the one or more thoracicimpedance-indicating signal characteristics is optionally attenuated. Invarious examples, one or both of a timing circuit or a cardiac sensorcircuit is used to synchronize the thoracic impedance-indicating signalcharacteristic measurements, such as to a refractory portion of asubject's cardiac cycle.

At 906, the one or more thoracic impedance-indicating signalcharacteristic measurements are compared to histogram bin subranges toidentify an appropriate histogram bin for the measurement. At 908, a bincount of the appropriate histogram bin is optionally incremented, suchas by incrementing a histogram bin counter or memory location storedcount value. At 909, a decision is made as to whether or not completehistogram information has been obtained. If not, the process returns to902. If it is determined that complete histogram information has beenobtained, the process continues to 910. At 910, a first histogram isoptionally overwritten with a later second histogram. In this way, newlyacquired histograms can overwrite older histograms, such as to prolongbattery life of a device associated with the memory storage device.

At 912, one or more histogram bins representative of an upper-quartilehistogram portion or an intra-quartile range are optionally selected andprocessed, such as via a processor circuit (see at 916). At 914, one orboth of a short-term histogram or a baseline histogram is optionallyupdated using information about thoracic impedance-indicating signalcharacteristic measured over a period of time. The short-term andbaseline histograms can be used to compute and provide a lung fluidstatus indication. In various examples, the lung fluid status indicationprovides an indication of the presence or absence of a thoracic fluidaccumulation event, such as a pulmonary edema event.

At 916, the lung fluid status indication is internally or externallycomputed using thoracic impedance histogram information. In one example,histogram bin count information from a particular intraday histogram isused to compute the lung fluid status indication. In another example, aplurality of intraday histograms are aggregated and used to compute thelung fluid status indication. In yet another example, the lung fluidstatus indication is computed using a deviation between one or morehistogram bins of a short-term histogram array and one or morecorresponding histogram bins of a baseline histogram array.

At 918, a subject is alerted to a detected presence of thoracic fluidaccumulation if the computed lung fluid status indication is beyond someprogrammed limit. At 920, a regimen for application to the subject isinitiated or adjusted in response to the computed lung fluid statusindication.

CONCLUSION

Chronic diseases, such as heart failure, require close medicalmanagement to reduce hospitalizations, morbidity and mortality, assubjects with heart failure live in a delicate balance. Because suchdisease status evolves with time, frequent caregiver follow-upexaminations are often necessary. This conventional approach of periodicfollow-up is unsatisfactory for diseases like heart failure, in whichacute, life-threatening exacerbations, such as pulmonary edema, candevelop between follow-up examinations. Pulmonary edema is a seriousmedical condition in which an excess amount of fluid accumulates in oraround a subject's lungs. This condition can, and often does, resultfrom heart failure. Pulmonary edema can require immediate care. While itcan sometimes prove fatal, the outlook for subjects possessing pulmonaryedema can be good upon early detection and prompt treatment.

Advantageously, the present systems and methods may provide for enhancedthoracic fluid monitoring via less complex data processing and thus, mayprovide a timelier, more accurate, and potentially cheaper detection ofpulmonary edema or other thoracic fluid accumulation than is currentlyavailable. In this way, caregivers and heart failure subjects can beprovided with a better tool to manage pulmonary edema, and ultimately,heart failure. Such detection is made possible by, among other things,storing at least one thoracic impedance-indicating signal characteristicin one of a number of histogram bins, each histogram bin numericallyrepresenting a different subrange of thoracic impedance-indicatingsignal characteristic values from a range of expected signal values. Inone example, thoracic fluid monitoring is made less complex by usinginformation about a count of thoracic impedance signal values stored inone or more of the histogram bins to compute a lung fluid statusindication. In another example, thoracic fluid monitoring is made moreaccurate by using information about a selected portion of a histogramarray, such as information about an upper-quartile portion orintra-quartile portion of the histogram array, to compute the lung fluidstatus indication.

CLOSING NOTES

The above Detailed Description includes references to the accompanyingdrawings, which form a part of the Detailed Description. The drawingsshow, by way of illustration, specific embodiments in which theinvention can be practiced. These embodiments are also referred toherein as “examples.” All publications, patents, and patent documentsreferred to in this document are incorporated by reference herein intheir entirety, as though individually incorporated by reference. In theevent of inconsistent usages between this document and those documentsso incorporated by reference, the usage in the incorporated reference(s)should be considered supplementary to that of this document; forirreconcilable inconsistencies, the usage in this document controls.

In this document, the terms “a” or “an” are used, as is common in patentdocuments, to include one or more than one, independent of any otherinstances or usages of “at least one” or “one or more.” In thisdocument, the term “or” is used to refer to a nonexclusive or, such that“A or B” includes “A but not B,” “B but not A,” and “A and B,” unlessotherwise indicated. In this document, the phrase “implantable medicaldevice” or simply “IMD” is used to include, but is not limited to,implantable cardiac rhythm management (CRM) systems such as pacemakers,cardioverters/defibrillators, pacemakers/defibrillators, biventricularor other multi-site resynchronization or coordination devices such ascardiac resynchronization therapy (CRT) device, subject monitoringsystems, neural modulation systems, and drug delivery systems. In theappended claims, the terms “including” and “in which” are used as theplain-English equivalents of the respective terms “comprising” and“wherein.” Also, in the following claims, the terms “including” and“comprising” are open-ended, that is, a system, device, article, orprocess that includes elements in addition to those listed after such aterm in a claim are still deemed to fall within the scope of that claim.Moreover, in the following claims, the terms “first,” “second,” and“third,” etc. are used merely as labels, and are not intended to imposenumerical requirements on their objects.

Method examples described herein can be machine-implemented orcomputer-implemented at least in part. Some examples can include acomputer-readable medium or machine-readable medium encoded withinstructions operable to configure an electronic device to performmethods as described in the above examples. An implementation of suchmethods can include code, such as microcode, assembly language code, ahigher-level language code, or the like. Such code can include computerreadable instructions for performing various methods. The code may formportions of computer program products. Further, the code may be tangiblystored on one or more volatile or non-volatile computer-readable mediaduring execution or at other times. These computer-readable media mayinclude, but are not limited to, hard disks, removable magnetic disks,removable optical disks (e.g., compact disks and digital video disks),magnetic cassettes, memory cards or sticks, random access memories(RAM's), read only memories (ROM's), and the like.

The above description is intended to be illustrative, and notrestrictive. For example, the above-described examples (or one or morefeatures thereof) may be used in combination with each other. Otherembodiments can be used, such as by one of ordinary skill in the artupon reviewing the above description. Also, in the above DetailedDescription, various features may be grouped together to streamline thedisclosure. This should not be interpreted as intending that anunclaimed disclosed feature is essential to any claim. Rather, inventivesubject matter may lie in less than all features of a particulardisclosed embodiment. In addition, while the majority of this patentdocument discusses the monitoring of fluid in a thoracic region of asubject, the present systems and methods can be used in ways similar tothose discussed herein to monitor fluid accumulation in other regions ofa subject's body. Thus, the following claims are hereby incorporatedinto the Detailed Description, with each claim standing on its own as aseparate embodiment. The scope of the invention should be determinedwith reference to the appended claims, along with the full scope ofequivalents to which such claims are entitled.

The Abstract is provided to comply with 37 C.F.R. §1.72(b), to allow thereader to quickly ascertain the nature of the technical disclosure. Itis submitted with the understanding that it will not be used tointerpret or limit the scope or meaning of the claims.

1. (canceled)
 2. A system comprising: an electrical impedancemeasurement circuit configured to measure a value representative of oneor more thoracic impedance-indicating signal characteristics, includingat least a liquid status component, using information about electricalenergy injected bet wen two or more electrodes and a potentialdifference created thereby between the same or different two or moreelectrodes; and a memory circuit including a number of histogram bins,each bin representing a subrange of thoracic impedance-indicating signalcharacteristic values, including values indicative of a liquid status,the memory circuit configured to store the value representative of theone or more thoracic impedance-indicating signal characteristics,including at least the liquid status component, into one of thehistogram bins having a numerically inclusive subrange; and a processorcircuit including an input to receive and use information about thevalues representative of the one or more thoracic impedance-indicatingsignal characteristics, including at least the liquid status component,stored in the histogram to provide a heart failure status indication. 3.The system of claim 2, comprising a trigger circuit to trigger athoracic impedance-indicating measurement synchronized with a refractoryportion of a subject's cardiac cycle, wherein the trigger circuitcomprises at least one of a timing circuit or a cardiac sensor circuit.4. The system of claim 2, comprising a posture sensor configured toproduce a posture signal indicative of a posture of a subject, theposture sensor configured to trigger a thoracic impedance-indicatingmeasurement when the posture signal is indicative of a uprightorientation.
 5. The system of claim 2, wherein the memory circuitincludes a counter circuit configured to count the number of valuesstored in a histogram bin.
 6. The system of claim 5, wherein theprocessor circuit is configured to use information about the count ofthe histogram bin to compute and provide the heart failure statusindication.
 7. The system of claim 2, comprising a histogram-selectivecircuit configured to select one or more histogram bins representativeof a reduced subrange of the histogram.
 8. The system of claim 7,wherein the processor circuit is configured to use information about avalue representative of the reduced subrange to compute and provide theheart failure status indication, wherein the reduced subrange representsan upper-percentile of the histogram or an intra-percentile range of thehistogram.
 9. The system of claim 8, wherein the information about thevalue representative of the reduced subrange includes information abouta central tendency of one or more values stored in the selected one ormore histogram bins, which are representative of the reduced subrange.10. The system of claim 2, comprising a comparator circuit configured tocompute a deviation between one or more histogram bins previouslyreceived from the memory circuit and one or more corresponding baselinehistogram bins having the same numerical subrange; and wherein theprocessor circuit is configured to use information about the deviationto compute and provide the heart failure status indication.
 11. Thesystem of claim 10, wherein the deviation is between an average ofthoracic impedance signal characteristic data of the one or morehistogram bins previously received and thoracic impedance signalcharacteristic data of the one or more baseline histogram bins.
 12. Thesystem of claim 2, comprising an external user-interface devicecommunicatively coupled to the implantable medical device and includinga user-detectable indication, the user-detectable indication configuredto provide a display of at least one of received information aboutthoracic impedance signal characteristic data of one or more histogrambins, a deviation trend between such received information andcorresponding information of one or more baseline histogram bins, or thecomputed hear failure status indication.
 13. A method comprising:measuring a thoracic impedance-indicating signal characteristicincluding a liquid status component; storing a value representative ofthe thoracic impedance-indicating signal characteristic, including theliquid status component, in a histogram that includes a plurality ofhistogram bins representing corresponding subranges of thoracicimpedance-indicating signal characteristic values, including valuesindicative of a liquid status; and computing and providing a heartfailure status indication using histogram information about the valuesrepresentative of the thoracic impedance-indicating signalcharacteristic stored in the plurality of histogram bins, including theliquid status component.
 14. The method of claim 13, comprisingattenuating a cardiac stroke component of the thoracicimpedance-indicating signal, including synchronizing the thoracicimpedance-indicating signal measurement to a specified portion of asubject's cardiac cycle.
 15. The method of claim 13, comprisingselecting one or more histogram bins representative of a subrange of thehistogram; and using information about a value representative of the oneor more bins representative of the subrange to provide the heart failurestatus indication.
 16. The method of claim 13, comprising overwriting afirst histogram comprising first histogram bins with a second histogramcomprising second histogram bins, the second histogram comprising dataacquired later in time than for the first histogram array.
 17. Themethod of claim 13, comprising initiating or adjusting a regimen inresponse to the heart failure status indication.
 18. The method of claim13, comprising triggering the thoracic impedance-indicating signalcharacteristic measurement when a posture signal indicative of a uprightorientation is measured.
 19. The method of claim 13, wherein storing thevalue representative of the thoracic impedance-indicating signalcharacteristic includes incrementing a count associated with a histogrambin; and wherein computing the heart failure status indication includesusing count information from the histogram.
 20. The method of claim 19,comprising aggregating count information from each of the histogrambins; and using the aggregated count information to compute the heartfailure status indication.
 21. The method of claim 13, comprisingaggregating thoracic impedance-indicating signal characteristicinformation from a plurality of intraday histograms; and using theaggregated thoracic impedance signal characteristic information tocompute the heart failure status indication.